Specimen radiography with tomosynthesis in a cabinet with geometric magnification

ABSTRACT

The aspects of the present disclosure are directed to a method and system for producing tomosynthesis images of a breast specimen with the capability of attaining images with geometric magnification. In one embodiment, an x-ray source delivers x-rays through a specimen of excised tissue and forms an image at a digital x-ray detector with the resultant image enlarging as the specimen is moved closer to the x-ray source. Multiple x-ray images are taken as the x-ray source moves relative to the stationary breast specimen. The source may travel substantially along a path while the detector remains stationary throughout and the source remains substantially equidistant from the specimen platform. The set of x-ray image data taken at the different points are combined to form a tomosynthesis image that can be viewed in different formats, alone or as an adjunct to conventional specimen radiography.

CROSS-REFERENCE TO RELATED APPLICATIONS

This application claims priority to and the benefit of U.S. patentapplication Ser. No. 15/696,341, filed Sep. 6, 2017, currently pending,which, in turn, claims priority to and the benefit of U.S. ProvisionalPatent Application Ser. No. 62/384,303 filed Sep. 7, 2016, thedisclosures of which are incorporated herein by reference in theirentirety.

BACKGROUND Field of the Present Disclosure

The aspects of the disclosed embodiments are directed to the field ofcabinet x-ray imaging of excised human tissue, and more specifically, toa system and method for obtaining and processing cabinet x-ray imagedata for tomosynthesis reconstruction allowing for a three-dimensionalimage of the specimen with the capability of attaining images of thespecimen with geometric magnification and the purpose of such devices,as described in U.S. Pat. No. 9,138,193 Lowe, et. al., entitled“Specimen Radiography with Tomosynthesis in a Cabinet,” the disclosureof which is hereby incorporated by reference in its entirely in thepresent application.

Description of the Related Art

Imaging of a patient's tissue has become a common screening tool and/ordiagnostic aid in modern medicine. Breast cancer remains an importantthreat to women's health and is the most common cancer among womentoday. One strategy for dealing with breast cancer is early detection ofthe cancer so that it may be treated prior to the cancer metastasizingthroughout the body. This causes an increase in the number of surgicalprocedures performed involving excision of cancerous tissue orcalcifications, such as ductal carcinoma in situ (DCIS).

The excision of Ductal carcinoma in situ (DCIS) is a challenging task.In order to assure that the complete DCIS lump including a cancer-freemargin has been excised, the following steps may be undertaken. Apre-operational planning based on mammograms is performed carefully inorder to assess the size and the location of the lump. The location ofthe lump is marked utilizing guide wires/markers. During the lumpectomy,the excised tissue is examined using x-ray imaging in order to assesswhether its margin is cancer-free. If it is found that the excisedspecimen has an insufficient margin of cancer-free tissue, the surgeonremoves more tissue.

Currently, x-ray images obtained are only available in two-dimensionalmode and as such orthogonal views of the sample must be obtained byphysically rotating the specimen to verify the margins. The breastsurgeon relies on the radiogram to verify removal of the complete lump.If necessary, the breast surgeon may have to identify additional breasttissue that must be excised to ensure a clear margin. This can be anerror prone and time consuming task that is performed under significanttime pressure whilst the anesthetized patient is still lying on theoperating table.

In typical x-ray imaging, a patient's breast sample is immobilized andcontained in a specimen container. The sample is placed between an x-raysource and a digital imaging device (detector) to create atwo-dimensional radiographic image of the sample. To ensure that marginsare attained, at least 2 orthogonal images must be taken of the sample(90 degrees apart). The problem that arises with the above scenario isthat the tissue, being somewhat fluid, may displace when it is imaged ineither position, which may cause a false measurement to the breastsurgeon. It would be advantageous to be able to image the sample from agreater number of different positions of the source and receptorrelative to the sample while maintaining the sample stationary or in afixed position.

Digital tomosynthesis combines digital image capture and processing withsimple tube/detector motion as used in conventional radiographictomography. Although there are some similarities to CT, it is a separatetechnique. In CT, the source/detector makes a complete 360-degreerotation about the subject obtaining a complete set of data from whichimages may be reconstructed. In digital tomosynthesis, a small change offlux created by only a small rotation angle with a small number ofexposures are used. This set of data can be digitally processed to yieldimages similar to conventional tomography with a limited depth of field.However, because the image processing is digital, a series of slices atdifferent depths and with different thicknesses can be reconstructedfrom the same acquisition, saving time.

Image data taken at the different imaging positions can be processed togenerate tomosynthetic images of selected slices of the sample. Theimages can be of thin slices, essentially planar sections through thespecimen, as in CT slices. Alternatively they can be varying thickness.

The isocenter of the image acquisition geometry is located below thesample, on the surface of the detector. The phase shifts created as aresult of this arrangement are compensated for, while processing theresultant dataset. The tomosynthetic images are then generated from thegenerated data set.

There may be cases where magnification of the specimen should beobtained to provide a better image or visualization of the anomaliespresent. Digital magnification can distort and/or pixelate an image atan “×” magnification whereas a geometric magnification would provide amagnification of an “×” power without any distortion of the sample.

It is believed that no cabinet specimen tomosynthesis systems utilizinggeometric magnification are commercially available currently forclinical use in specimen imaging, and that improvements in x-ray imagingand tomosynthesis are a desired goal. Accordingly, it is believed thatthere is a need for improved and practical tomosynthesis of breastspecimens with the capability of geometric magnification

It would be advantageous to have a cabinet x-ray system for specimenimaging that could create, via digital tomosynthesis, athree-dimensional image for the breast surgeon to ensure that a propermargin around the diseased tissue has been excised in an expedientmanner.

To address this, in one aspect of the present disclosure include asample tray holding the specimen may be elevated in the sample chamberabove the detector to allow for a geometric magnification of thespecimen imaged and to create images which would compensate and/ordelete digital distortion.

SUMMARY

In one embodiment, a cabinet x-ray system for of obtaining geometricmagnifying specimen x-ray images, projection x-ray images, andreconstructed tomosynthetic x-ray images of the specimen is provided.The system includes a moveable cabinet defining a walled enclosuresurrounding an interior chamber and a door configured to cover theinterior chamber; an x-ray source, a flat panel digital x-ray detector,a specimen platform including a magnification tray that is positioned ata distance above the flat panel digital x-ray detector to facilitategeometric magnification imaging of the specimen in the cabinet and amotion control mechanism configured for moving the x-ray source to oralong a plurality of positions within the interior chamber relative tothe specimen disposed on the specimen platform; and a controller. Thecontroller is configured to selectively energize the x-ray source toemit x-rays through the specimen to the flat panel digital x-raydetector at selected positions of the x-ray source relative to thespecimen such that the isocenter of the emitted x-rays at the selectedpositions is located at the flat panel digital x-ray detector surface,control the flat panel digital x-ray detector to collect projectionx-ray images of the specimen when the x-ray source is energized at theselected positions, wherein one of the projection x-ray images is atwo-dimensional x-ray image taken at standard imaging angle of about 0°;create a tomosynthetic x-ray image reconstructed from a collection ofprojection x-ray images, process the collection of the projection x-rayimages in the controller into one or more reconstructed tomosyntheticx-ray images representing a volume of the specimen and relating to oneor more image planes that are selectively the same or different fromthat of the two-dimensional x-ray image and selectively display thetwo-dimensional x-ray image and the one or more reconstructedtomosynthetic x-ray images.

In another embodiment, a method for obtaining x-ray images of a specimenin a cabinet x-ray system, processing and displaying a two-dimensionalx-ray specimen radiography image and projection x-ray images of thespecimen is provided, wherein the cabinet x-ray system includes amoveable cabinet defining a walled enclosure surrounding an interiorchamber and a door configured to cover the interior chamber; an x-raysource, a flat panel digital x-ray detector, a specimen platformincluding a magnification tray that is positioned at a distance abovethe flat panel digital x-ray detector to facilitate geometricmagnification imaging of the specimen, and a motion control mechanismconfigured for moving the x-ray source to or along a plurality ofpositions within the interior chamber relative to the specimen disposedon the specimen platform; and a controller configured to selectivelyenergize the x-ray source to emit x-rays through the specimen to theflat panel digital x-ray detector at selected positions of the x-raysource relative to the specimen. The method includes controlling theflat panel digital x-ray detector to collect projection x-ray images ofthe specimen when the x-ray source is energized at the selectedpositions such that the isocenter of the emitted x-rays at the selectedpositions is located at the detector surface, wherein one of theprojection x-ray images is a two-dimensional x-ray image taken atstandard imaging angle of about 0°; creating a tomosynthetic x-ray imagereconstructed from a collection of projection x-ray images; processingthe collection of the projection x-ray images in the controller into oneor more reconstructed tomosynthetic x-ray images representing a volumeof the specimen and relating to one or more image planes that areselectively the same or different from that of the two-dimensional x-rayimage; and selectively displaying the two-dimensional x-ray image andthe one or more reconstructed tomosynthetic x-ray images.

In yet another embodiment, a cabinet x-ray system for of obtaining x-rayimages, projection x-ray images, and reconstructed tomosynthetic x-rayimages of a specimen is provided. The system Includes a cabinet definingan interior chamber, an x-ray source, an x-ray detector, a specimenplatform, a motion control mechanism and a controller. The specimenplatform includes a magnification tray that is positioned at a distanceabove the flat panel digital x-ray detector to facilitate geometricmagnification imaging of the specimen in the cabinet. The motion controlmechanism is configured for moving the x-ray source to or along aplurality of positions within the interior chamber relative to thespecimen disposed on the specimen platform. The controller is configuredto selectively energize the x-ray source to emit x-rays through thespecimen to the x-ray detector at selected positions of the x-ray sourcerelative to the specimen such that the isocenter of the emitted x-raysat the selected positions is located at a surface of the x-ray detector;control the x-ray detector to collect projection x-ray images of thespecimen when the x-ray source is energized at the selected positions,wherein one of the projection x-ray images is a two-dimensional x-rayimage taken at standard imaging angle of approximately 0°; create atomosynthetic x-ray image reconstructed from a collection of projectionx-ray images; process the collection of the projection x-ray images inthe controller into one or more reconstructed tomosynthetic x-ray imagesrepresenting a volume of the specimen and relating to one or more imageplanes that are selectively the same or different from that of thetwo-dimensional x-ray image; and selectively display the two-dimensionalx-ray image and the one or more reconstructed tomosynthetic x-rayimages.

In still another embodiment, a method for obtaining x-ray images of aspecimen in a cabinet x-ray system, processing and displaying atwo-dimensional x-ray image and projection x-ray images of the specimenis provided. The cabinet x-ray system includes a cabinet defining aninterior chamber; an x-ray source, an x-ray detector, a specimenplatform includes a magnification tray that is positioned at a distanceabove the flat panel digital x-ray detector to facilitate geometricmagnification imaging of the specimen, and a motion control mechanismconfigured for moving the x-ray source to or along a plurality ofpositions within the interior chamber relative to the specimen disposedon the specimen platform; and a controller configured to selectivelyenergize the x-ray source to emit x-rays through the specimen to thex-ray detector at selected positions of the x-ray source relative to thespecimen. The method comprises includes controlling the x-ray detectorto collect projection x-ray images of the specimen when the x-ray sourceis energized at the selected positions such that the isocenter of theemitted x-rays at the selected positions is located at a surface of thex-ray detector, wherein one of the projection x-ray images is atwo-dimensional x-ray image taken at standard imaging angle ofapproximately 0°; creating a tomosynthetic x-ray image reconstructedfrom a collection of projection x-ray images; processing the collectionof the projection x-ray images in the controller into one or morereconstructed tomosynthetic x-ray images representing a volume of thespecimen and relating to one or more image planes that are selectivelythe same or different from that of the two-dimensional x-ray image; andselectively displaying the two-dimensional x-ray image and the one ormore reconstructed tomosynthetic x-ray images.

As described herein, the exemplary embodiments overcome one or more ofthe above or other disadvantages known in the art. In one embodiment,the aspects of the present disclosure are directed to a method andsystem for obtaining breast specimen x-ray images, projectiontomosynthesis x-ray images, and reconstructed tomosynthesis x-ray imagesof a patient's breast specimen (also referred to herein as a “sample”)and or performing digital tomosynthesis on an object. In one embodiment,the method and system includes an x-ray source, a flat panel digitalx-ray detector, a specimen platform or container and a motion controlmechanism configured for moving the source relative to the specimen(collectively referred to herein as the “unit”). The x-ray source isselectively energized to emit x-rays through the sample to the detectorat selected positions of the source relative to the sample. The detectoris controlled to collect projection x-ray images of the sample when thesource is energized at the selected positions. One of the projectionimages is a two-dimensional image taken at standard imaging angle of 0°,and a tomosynthetic image reconstructed from a collection oftomosynthesis projection images is created.

In accordance with the aspects of the disclosed embodiments, the x-raysource moves around the stationary sample, typically, but notnecessarily, in an arc. While the detector may rotate, in accordancewith one aspect of the present disclosure, the detector remainsstationary to maintain an equidistant center point. The x-ray data takenat each of a number of positions of the source relative to the sample isprocessed to form images, where two or more of the differing imagingpositions are utilized to form a digital tomosynthesis image.

The specimen container/sample may be situated on a tray located directlyabove the detector to attain a 1:1 imaging as well as be able to beelevated on the tray to a multitude of elevations above the detector tocreate images with geometric magnification. The collection of thetomosynthesis projection images is processed, typically using acomputing device or other processor, into one or more reconstructedimages representing a volume of the sample and relating to one or moreimage planes that are selectively the same or different from that of the2-D image. The 2-D image and the reconstructed tomosynthesis images areselectively displayed.

This above allows the clinician verification via a display of either athree-dimensional or slice/multiplanar view of the sample that marginshave been attained by the surgeon.

In a further aspect, the disclosed embodiments are directed to methodand system for selectively using the same x-ray equipment to take,process and display a 2-D specimen radiography image and projectiontomosynthesis images. In one embodiment, this includes an x-ray source,a flat panel digital x-ray detector, and a specimen platform orcontainer and a motion control mechanism configured for moving thesource relative to the specimen (collectively referred to herein as the“unit”). The x-ray source is selectively energized to emit x-raysthrough the sample or specimen to the detector at selected positions ofthe source relative of the sample. The detector is controlled to collectprojections x-ray images of the sample when the source is energized atthe selected positions. One of the projection images is atwo-dimensional image taken at standard imaging angle of 0° and atomosynthetic image reconstructed from a collection of projection imagesis created.

The collection of the tomosynthesis projections images is processed by acomputer or other processor into one or more reconstructed imagesrepresenting a volume of the sample and relating to one or more imageplanes that are selectively the same or different from that of the 2-Dspecimen image. The 2-D specimen image and the reconstructedtomosynthesis images are selectively displayed.

The above aspects of the disclosed embodiments overcome the deficienciesof the prior art by advantageously allowing the operator to be able toview the sample in a three-dimensional mode and take varying slices toensure that the surgeon has attained a correct margin in an expedientmanner without having to manipulate the excised sample.

These and other aspects and advantages of the exemplary embodiments willbecome apparent from the following detailed description considered inconjunction with the accompanying drawings. It is to be understood,however, that the drawings are designed solely for purposes ofillustration and not as a definition of the limits of the invention, forwhich reference should be made to the appended claims. Moreover, thedrawings are not necessarily drawn to scale and that, unless otherwiseindicated, they are merely intended to conceptually illustrate thestructures and procedures described herein. In addition, any suitablesize, shape or type of elements or materials could be used.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1—Schematically illustrates a front view of an X-ray source, aspecimen/sample, and a digital detector, where the X-ray source movesrelative to the specimen for imaging the specimen at different angles,in one embodiment of a system incorporating aspects of the presentdisclosure.

FIG. 2—Schematically illustrates an exemplary orientation of the X-raysource, specimen, and digital detector as viewed when the door of thecabinet is open, in one embodiment of a system incorporating aspects ofthe present disclosure.

FIG. 3—Displays an exemplary workflow/flowchart of an aspect of thedisclosed embodiments.

FIG. 4—Displays an example of an X-ray Cabinet System incorporatingaspects of the present disclosure.

FIG. 5—Displays the sample chamber of the embodiment of FIG. 4 with theswing arm and a detector.

FIG. 6—Displays the lateral view of the X-ray source of the embodimentof FIG. 4 mounted to the top of the swing arm.

FIGS. 7A, 7B and 7C—Displays the results of the imaging of an apple atmultiple depth cuts after tomosynthesis reconstruction in a cabinetX-ray system incorporating aspects of the present disclosure.

FIG. 8—Displays FIG. 2 but with the sample geometrically magnified on araised sample tray as well as the magnification shelfs brackets in oneembodiment of a system incorporating aspects of the present disclosure .

FIG. 9—Displays FIG. 1 but with the sample geometrically magnified on araised sample tray in one embodiment of a system incorporating aspectsof the present disclosure.

FIGS. 10A, 10B, and 10C—Display examples and theories of x-ray geometricmagnification

DETAILED DESCRIPTION

The systems and methods of the disclosed embodiments address the needsof the art by providing tomosynthesis apparatus and techniques forimaging breast specimens that overcome the shortfall of the datareceived from two-dimensional imaging systems. The aspects of thedisclosed embodiments enable the use of tomosynthesis to efficientlyprovide accurate three-dimensional imaging of a specimen in whichoverlapping images having differing attenuation characteristics byapplying a three-dimensional reconstruction algorithm all in an x-raycabinet with the option of providing geometric magnification of thespecimen.

As used herein, the term “computer,” “computer system” or “processor”refers to any suitable device operable to accept input, process theinput according to predefined rules, and produce output, including, forexample, a server, workstation, personal computer, network computer,wireless telephone, personal digital assistant, one or moremicroprocessors within these or other devices, or any other suitableprocessing device with accessible memory.

The term “computer program” or “software” refers to any non-transitorymachine readable instructions, program or library of routines capable ofexecuting on a computer or computer system including computer readableprogram code.

Specimen Tomography is a three-dimensional specimen imaging system. Itinvolves acquiring images of a sample at multiple viewpoints, typicallyover an arc or linear path. The three-dimensional image is constructedby the reconstruction of the multiple image data set. One embodiment ofa system incorporating aspects of the present disclosure is illustratedin FIG. 1. The system is totally enclosed or housed in an X-ray cabinet22. The aspects of the present disclosure include arc or linear travelof the x-ray source (10) over about a 20° to about a 50° arc, preferablyabout 30°, more preferably about 20°. The movement can be clockwise orcounter clockwise along a path, which includes for example, one or more,or a combination thereof, of the following exemplary ranges: betweenapproximately 350° (reference 12) to 0° (reference 14) to 10° (reference16) or between approximately 340° (reference 12) to 0° (reference 14) to20° (reference 16) or between approximately 335° (reference 12) to 0°(reference 14) to 25° (reference 16). The ranges recited herein areintended to be approximate and inclusive of start and endpoints. Thedetector 20 is stationary as is the sample 18 and is an x-ray detectorand can include, for example, a flat panel x-ray detector, a flat paneldigital x-ray detector. The reference “C” at each of the positions 12,14, 16 of the X-ray source 10 in FIG. 1 refers to the point source ofthe X-ray beam. The reference “M” refers to the spread or fan of theX-ray beam.

In operation, source 10 is energized to emit an x-ray beam throughoutits travel. The x-ray beam travels through the sample 18 to the detector16 and the multiple images collected at varying angles are stored andthen utilized for the tomosynthesis reconstruction. With the sample 18,also referred to as the “object” or “imaging object”, sitting on thedetector 16 a 1:1 geometric magnification image is attained.

Different embodiments can utilize different ranges of motion of one ormore of the source 10 and detector 20 as well as changing the angularityof one or both. The inventive aspects of the present disclosure differfrom prior systems in that either both the detector and source moveand/or the isocenter is above the sample and not at the detectorsurface. In accordance with the aspects of the present disclosure, inone embodiment, the source 10 may be configured to move or rotate, as isdescribed herein, while the detector 20 is configured to remainstationary or in a fixed position.

Detector 20 and associated electronics generate image data in digitalform for each pixel at each of the angular positions of source 10 andtranslations positions of the detector 20 relative to the sample 18.While only three positions are illustrated in FIG. 1, in practice moreimages are taken at differing angles, i.e. approximately every 1° ofrotation or motion of source 10.

In operation, X-ray source 10 is energized to emit an X-ray beam,generally throughout its travel along one or more of the paths orpositions described above. The X-ray beam travels through the sample 18to the detector 20 and the multiple images collected at varying anglesare stored and then utilized for the tomosynthesis reconstruction. TheX-ray source 10 may range from about 0 kVp to about 90 kVp, preferably a50 kVp 1000 μa X-ray source.

Different embodiments of the present disclosure can utilize differentranges of motion of one or more of the X-ray source 10 and detector 20as well as changing the angularity of one or both. The inventive aspectsof the present disclosure differ from the prior art in that in prior artsystems either the detector and X-ray source 10 and/or the isocenter isabove the sample and not at the detector surface. In accordance with theaspects of the present disclosure, in one embodiment, the X-ray source10 is configured to move, as is described herein, while the detector 20is configured to remain stationary or in a fixed position.

The detector 20 and associated electronics generate image data indigital form for each pixel at each of the angular positions 12, 14, 16of X-ray source 10 and translation positions of the detector 20 relativeto the sample 18. While only three positions 12, 14, 16 are illustratedin FIG. 1, in practice more images are taken at differing angles. Forexample, in one embodiment, images can be taken at approximately every1° of rotation or motion of source 10.

FIG. 2 schematically illustrates one embodiment of the orientation ofthe X-ray source 10 as seen when the door 24 is opened and the X-raysource 10 is locate at approximately 0°, reference point 14 in thisexample, within the X-ray cabinet 22. In this embodiment, the motion ofthe X-ray source 10 can generally occur from the back to the front ofthe X-ray cabinet 22 with the detector 20 oriented, or otherwisedisposed, at the base 26 of the X-ray cabinet 22, within the X-raycabinet chamber 28. In one embodiment, the detector 20 is suitablycoupled to the base 26 of the X-ray cabinet 22. The X-ray spread in thisexample can be from about 0 kVp to about 50 kVp with the systempreferably utilizing an AEC (Automatic Exposure Control) to ascertainthe optimal setting to image the object or sample 18 being examined.

In one embodiment, the detector 20, X-ray source 10, and the swing arm60 (FIG. 5) servo mechanism are controlled via a combination of one ormore of software and hardware, such as non-transitory machine readableinstructions stored in a memory that are executable by one or moreprocessors. On example of such a configuration can include controllercards of a computer 470 (FIG. 4), such as a MS Windows based computer.In one embodiment, non-transitory machine readable instructions beingexecuted by one or more processors of the computer 470 is utilized tocompile data received from the detector 20 and present resulting imagesto a suitable display or monitor 472 (FIG. 4) at each imaging position,such as positions 12, 14 and 16 shown in FIG. 1, the detector 20generates the respective digital values for the pixels in atwo-dimensional array. The size of detector 20 may range, for example,from about 5.08 centimeters by 5.08 centimeters to about 40.64centimeters by 40.64 centimeters, preferably about 12.7 centimeters by15.24 centimeters. In one example, detector 20 has a rectangular arrayof approximately 1536×1944 pixels with a pixel size of 74.8 micrometers.The image dataset attained at each respective position may be processedeither at the full spatial resolution of detector 20 or at a lowerspatial resolution by overlapping or binning a specified number ofpixels in a single combined pixel value.

For example, if we bin at a 2×2 ratio, then there would be an effectivespatial resolution of approximately 149.6 micrometers. This binning maybe achieved within the original programming of the detector 20 or withinthe computer 470 providing the tomosynthetic compilation and image.

FIG. 3 illustrates one embodiment of an exemplary workflow frominitiating 302 the system 100 through imaging, reconstruction anddisplay 324 of data images collected of the sample 18.

As will be generally understood, the system exemplified in FIG. 1, forexample, is initiated 302, the X-ray cabinet door 24 opened 304, and thesample 18 placed into 306 the X-ray cabinet chamber 28. As shown in FIG.2, for example, the sample 18 is positioned on the detector 20 in asuitable manner. The door 24 is closed 308.

The data and information regarding the sample 18, including any othersuitable information or settings relevant to the imaging process andprocedure, is entered 310 into the computer 470. The scan is initiated312. The system 100 will take 314 scout or 2-D images at Top DeadCenter, which for purposes of this example is position 14 of FIGS. 1 and2. The X-ray source 10 can then be moved to other positions, such aspositions 12 and 16, and the detector 20 can be used to capture 316images at various increments along the travel path of the X-ray source10, such as about every 1 degree.

The captured images are stored 318 and digital tomosynthesis isperformed 320. The tomosynthesis image is then displayed 324.

FIG. 4 shows one embodiment of an X-ray Cabinet

System 400 incorporating aspects of the present disclosure. In thisembodiment, the X-ray Cabinet System 400 is mounted on wheels 458 toallow easy portability. In alternate embodiments, the X-ray CabinetSystem 400 can be mounted on any suitable base or transport mechanism.The cabinet 422 in this example, similar to the exemplary X-ray cabinet22 of FIG. 1, is constructed of a suitable material such as steel. Inone embodiment, the cabinet 422 comprises painted steel defining awalled enclosure with an opening or cabinet chamber 428. Within thecabinet chamber 428, behind door 424, resides an interior space forminga sample chamber 444, which in this example is constructed of stainlesssteel. Access to the sample chamber 444 is via an opening 446. In oneembodiment, the opening 446 of the sample chamber 444 has a suitabledoor or cover, such as a moveable cover 448. In one embodiment, themoveable cover 448 comprises a door which has a window of leaded glass.

Between the outer wall 421 of cabinet 422 and the sample chamber 444 aresheets of lead 452 that serve as shielding to reduce radiation leakageemitted from the X-ray source 10. In the example of FIG. 4, the X-raysource 10 is located in the upper part 456 of the cabinet 422, in thesource enclosure 468. The detector 20 is housed in the detectorenclosure 460 at an approximate midpoint 462 of the cabinet 422.

In one embodiment, a controller or computer 470 controls the collectionof data from the detector 20, controls the swing arm 60 shown in FIGS. 5& 6, and X-ray source 10. A monitor 472 displays the compiled data andcan, for example, be mounted on an articulating arm 474 that is attachedto the cabinet 422. The computer 470 receives commands and other inputinformation entered by the operator via a user interface 476, such as akeyboard and mouse for example. In one embodiment, the computer 470 cancomprise a touch screen or near touch screen device. Although theaspects of the disclosed embodiments will generally be described withrespect to a computer 470, it will be understood that the computer 470can comprise any suitable controller or computing device. Such computingdevices can include, but are not limited to, laptop computers, minicomputers, tablets and pad devices.

The computer 470 can be configured to communicate with the components ofthe X-ray cabinet system 400 in any suitable manner, including hardwiredand wireless communication. In one embodiment, the computer 470 can beconfigured to communicate over a network, such as a Local Area Networkor the Internet.

FIG. 5 shows a front interior view and FIG. 6 shows a lateral interiorview of the sample chamber of imaging unit cabinet of FIG. 4. In thisembodiment, a sample 18 is placed or otherwise disposed onto thedetector 20. Using the computer 470 shown in FIG. 4, the operator entersin the parameters for the scan via the user interface 476, which can bedisplayed on the monitor 472. As used herein, the term “display” or“monitor” means any type of device adapted to display information,including without limitation CRTs, LCDs, TFTs, plasma displays, LEDs,and fluorescent devices. The computer 470 then sends the appropriatecommands to the X-ray source 10 and detector 20 to activate imagecollection while the swing arm 60 is moving along a path or arc fromposition 14 to 12 to 16 (which are shown in FIGS. 1 and 5) or vice versaas described, which in this embodiment are at 345°, 0°, and 15°respectively with 0° at top dead center. At the end of the travel of theswing arm 60 at either position 12 or 16, the computer 470 issues thecommand to the X-ray source 10 and the detector 20 to cease operating.The individual 2-dimensional (2-D) images which were collected, in thisexample at 1° increments, are then tabulated in the computer 470 tocreate the tomosynthetic images. In one embodiment, the operator mayselect which images they wish via the user interface 476 as they arebeing displayed on the monitor 472. In one embodiment, the devices andcomponents of the X-ray cabinet system 400 are suitably communicativelycoupled together, including one or more of hard wire connections orwireless connections using a suitable wireless connection andcommunication transmission protocol, as will generally be understood.The X-ray cabinet system 400 can also be configured to transfer imagesvia USB, CD-ROM, or WIFI.

The dynamic imaging software of the disclosed embodiments reconstructsthree-dimensional images (tomosynthesis) from two-dimensional projectionimages in real-time and on-demand. The software offers the ability toexamine any slice depth, tilt the reconstruction plane for multiplanarviews and gives higher resolution magnifications. FIGS. 7A, 7B, and 7Cillustrate exemplary images of an apple using the above process.

FIG. 7A is an image of a slice of the apple at it's very top. 59 mm fromthe bottom. FIG. 7B is an image of an apple computed at 30.5 mm up fromthe detector, and FIG. 7C is a view of the apple computed at 13.5 mmfrom the bottom.

The dynamic imaging software reconstructs three-dimensional images(tomosynthesis) from two-dimensional projection images in real-time andon-demand. The software offers the ability to examine any slice depth,tilt the reconstruction plane for multiplanar views and gives higherresolution magnifications (FIG. 7). Real-time image reconstructionenables immediate review, higher throughput, and more efficientinterventional procedures reducing patient call backs and data storageneeds. Multiplanar reconstruction enables reconstruction to any depth,magnification and plane, giving the viewer the greater ability to viewand interrogate image data, thereby reducing the likelihood of missingsmall structures. Built-in filters allow higher in-plane resolution andimage quality during magnification for greater diagnostic confidence.Software is optimized for performance using GPU technology.

The reconstruction software provides the users greater flexibility andimproved visibility of the image data. It reconstructs images at anydepth specified by the user rather than at fixed slice increments. Withfixed slice increments, an object located between two reconstructedslices, such as a calcification, is blurred and can be potentiallymissed. The software can position the reconstruction plane so that anyobject is exactly in focus. This includes objects that are oriented atan angle to the detector; in the software the reconstruction plane canbe angled with respect to the detector plane.

Another embodiment of a system incorporating aspects of the presentdisclosure is illustrated in FIG. 8. FIG. 8 schematically illustratesthe orientation of the mechanism as seen when the door is opened and themechanism is located at approximately 0° 14, similar to FIG. 2. Motionof the source 10 will generally occur from the back to the front withthe detector 20 orientated at the base of the cabinet chamber 22. Thereference “C” refers to the point source of the X-ray beam. Thereference “M” refers to the spread or fan of the X-ray. Illustration isprovided when the sample is elevated above the detector on themagnification tray 30 to affect geometric magnification. Geometricmagnification is achieved by moving the movable magnification tray 30closer to the x-ray source 10 brackets on which the magnification tray30 is supported, the brackets being to mounted (permanently ortemporarily) to the sides (interior walls) of the cabinet at differentdistances from the detector 20. In this example, brackets 32 couldproduce a 2× magnification of sample 18 when magnification tray 30 withsample 18 is positioned on brackets 32 and brackets 34 could produce a1.5× magnification of sample 18 when magnification tray 30 with sample18 is positioned on brackets 34. However, these are exemplifiedmagnification powers and shelf bracket heights and are not to beconsidered limiting. If we affix shelf bracket 32 and the magnificationtray 30 closer to the x-ray source 10 we will attain a greater geometricmagnification—3× or more. The magnification tray 30 is normally keptoutside the x-ray chamber 28, for example, when sample 18 is positionedon detector 20, as illustrated, for example, in FIG. 1. and isconstructed of a radio translucent (x-ray transparent) material such asplastic or carbon fibre.

FIG. 9 schematically displays items as described in FIG. 1 but thedifference is that the sample is raised above the detector to effectgeometric magnification with distance above the detector 19 illustrated

FIG. 10A, 10B and 10C illustrate geometric magnification. Geometricmagnification results from the detector being farther away from theX-ray source than the object. In this regard, the source-detectordistance or SDD 510 (also called the source to image-receptor distanceor SID) is a measurement of the distance between the x-ray tube 10 andthe detector 20.

The estimated radiographic magnification factor (ERMF) is the ratio ofthe source-detector distance 510 (SDD) over the source-object distance512 (SOD).

The source-detector distance 510 (SDD) is roughly related to thesource-object distance 512 (SOD) and the object-detector distance 514(ODD) by the equation SOD 512+ODD 514=SDD 510.

Similar to a lens in photography, where the sample 18 is positionedrelative to the source 10 and detector 20 changes magnification andfield of view. Three terms are used to describe positioning:source-object distance 512 (SOD, where the object represents thesample); object-image distance 514 (OID, where the image is the detector20); and source-image distance (SID) or source detector distance 510(SDD). The effects of moving the sample 18 and detector 20 can be seenby the method of similar triangles. In the example as shown in FIGS.10A, 10B and 10C as the top triangles 512A, 512B and 512C (cross hatchfill) get shorter going from FIG. 10A to FIG. 10B to FIG. 10C, thebottom triangles 514A, 514B and 514C (checker fill) get longer and thebase of the triangles 526A, 526B and 526C gets wider effectingmagnification on the detector 20 and the magnification of the resultingimages 520, 522 and 524.

In FIG. 10B the sample 18 is moved away from the source 10 and theresultant image 520, 522, 524 goes down in size (less magnified) as thesample 18 moves closer to the detector 20. Differences in magnificationare exhibited by the differing triangle lengths and the resultant imagewhich represent the source-object distance 512 (SOD) and theobject-detector distance 514 (ODD). Preferably for geometricmagnification, the sample 18 is supported by a magnification tray 30 (inFIGS. 8 and 9) to be imaged.

Thus, while there have been shown and described and pointed outfundamental novel features of the invention as applied to the exemplaryembodiments thereof, it will be understood that various omissions andsubstitutions and changes in the form and details of devicesillustrated, and in their operation, may be made by those skilled in theart without departing from the spirit of the invention. For example, itis expressly intended that all combinations of those elements and/ormethod steps which perform substantially the same function insubstantially the same way to achieve the same results are within thescope of the invention. Moreover, it should be recognized thatstructures and/or elements and/or method steps shown and/or described inconnection with any disclosed form or embodiment of the invention may beincorporated in any other disclosed or described or suggested form orembodiment as a general matter of design choice. It is the intention,therefore, to be limited only as indicated by the scope of the claimsappended hereto.

1. A cabinet x-ray system for of obtaining geometric magnifying specimenx-ray images, projection x-ray images, and reconstructed tomosyntheticx-ray images of the specimen, the system comprising: a cabinet defininga walled enclosure surrounding an interior chamber and a door configuredto cover the interior chamber; an x-ray source, an x-ray detector, aspecimen platform including a magnification tray that is positioned at adistance above the x-ray detector to facilitate geometric magnificationimaging of the specimen in the cabinet and a motion control mechanismconfigured for moving the x-ray source to or along a plurality ofpositions within the interior chamber relative to the specimen disposedon the specimen platform; a controller configured to: a) selectivelyenergize the x-ray source to emit x-rays through the specimen to thex-ray detector at selected positions of the x-ray source relative to thespecimen such that the isocenter of the emitted x-rays at the selectedpositions is located at the x-ray detector surface, wherein thecontroller is configured to: b) control the x-ray detector to collectprojection x-ray images of the specimen when the x-ray source isenergized at the selected positions, wherein one of the projection x-rayimages is a two-dimensional x-ray image taken at standard imaging angleof about 0°; c) create a tomosynthetic x-ray image reconstructed from acollection of projection x-ray images; d) process the collection of theprojection x-ray images in the controller into one or more reconstructedtomosynthetic x-ray images representing a volume of the specimen andrelating to one or more image planes that are selectively the same ordifferent from that of the two-dimensional x-ray image; and e)selectively display the two-dimensional x-ray image and the one or morereconstructed tomosynthetic x-ray images.
 2. The cabinet x-ray system ofclaim 1, wherein the cabinet comprises a sampling chamber within theinterior chamber for containing the specimen.
 3. The cabinet x-raysystem of claim 1, wherein the specimen platform is configured forexcised tissue, organ or bone specimens.
 4. The cabinet x-ray system ofclaim 1, wherein the specimen platform is capable of being positionedwithin the chamber at a plurality of distances above the x-ray detectorto facilitate geometric magnification imaging of the specimen.
 5. Thecabinet x-ray system of claim 1, wherein the magnification tray is anon-metallic, radio-translucent material.
 6. The cabinet x-ray system ofclaim 1, further comprising an x-ray cabinet wherein the specimenplatform is configured for any organic or inorganic specimen that fitsinside the x-ray cabinet.
 7. The cabinet x-ray system of claim 1,wherein the controller is mounted in the cabinet.
 8. The cabinet x-raysystem of claim 1, wherein the x-ray source is a moveable x-ray source,the cabinet x-ray system including a device to move or position thex-ray source within the cabinet.
 9. The cabinet x-ray system of claim 1,wherein the motion control mechanism is configured to move the x-raysource along a path substantially defining an arc.
 10. The cabinet x-raysystem of claim 1, wherein the x-ray detector is in a stationary orfixed position within the cabinet.
 11. The cabinet x-ray system of claim1, wherein the motion control mechanism is configured to move the x-raysource along a path in a range from about 350° to 10° or from about 340°to 20° or vice versa or a maximum of about 335° to 25° or vice versa.12. The cabinet x-ray system of claim 1, wherein the motion controlmechanism is configured to move the x-ray source from back to front orfront to back in the cabinet.
 13. The cabinet x-ray system of claim 1,wherein the movement of the x-ray within the cabinet source is from sideto side such that the spread of the x-ray beam along the path is withinthe spread of the x-ray beam when the x-ray source is at the standardimaging angle of about 0°.
 14. The cabinet x-ray system of claim 1, inwhich the x-ray source is a minimum 50 kVp and 1000 μa X-ray source. 15.The cabinet x-ray system of claim 1, in which the x-ray source is amicro-focus X-ray source.
 16. The cabinet x-ray system of claim 1, inwhich the x-ray detector comprises a CMOS x-ray detector.
 17. Thecabinet x-ray system of claim 1, in which the controller is configuredto supply standard two-dimensional x-ray images.
 18. The cabinet x-raysystem of claim 1, in which the controller is configured to interpolatethe projection x-ray images gathered and calculate a tomosynthetic x-rayimage.
 19. The cabinet x-ray system of claim 1, wherein the controllercomprises one or more processors and computer readable program code ornon-transitory machine readable instructions, which when executed by theone or more processors of the controller, is configured to providebuilt-in filters allowing higher in-plane resolution and image qualityof the one or more reconstructed tomosynthetic x-ray images duringmagnification for greater diagnostic confidence.
 20. The cabinet x-raysystem of claim 1, wherein the controller is configured to reconstructthree-dimensional tomosynthetic x-ray images from two-dimensionalprojection x-ray images in real-time and on-demand.
 21. The cabinetx-ray system of claim 1, wherein the controller includes graphicprocessor unit (GPU) technology and is configured to deliver real-timethree-dimensional image reconstruction of tomosynthetic x-ray images byutilizing graphic processor unit (GPU) technology.
 22. The cabinet x-raysystem of claim 1, wherein the specimen platform is configured for abreast specimen of a person.
 23. The cabinet x-ray system of claim 1, inwhich the cabinet is a moveable cabinet.
 24. The cabinet x-ray system ofclaim 1, in which the x-ray detector is a digital x-ray detector. 25.The cabinet x-ray system of claim 24, in which the digital x-raydetector is a flat panel digital x-ray detector.